Blood dialysis apparatus having convenient controlling unit

ABSTRACT

A hemodialysis apparatus that carries out hemodialysis treatment by controlling dialysis conditions, wherein the hemodialysis treatment is carried out under dialysis conditions determined by defining the course of said chronological target blood indication level as a target control line, measuring the blood indication level at each measurement point (controlling point) in said chronological course, calculating the dialysis conditions with the use of said measured blood indication level and the target blood indication level at the next measurement point (controlling point) of said measurement point (controlling point) in the hemodialysis apparatus carrying out hemodialysis treatment by controlling dialysis conditions with the use of blood volume (BV level) or blood volume change as an indication level (hereinafter also referred to as blood indication level), to attain the target blood indication level at the next measurement point (controlling point). This apparatus has a simple control mechanism and has little risk of misoperation or out-of-control. An operator can easily handle it and the control can be quickly and precisely carried out. Therefore, the blood volume transits appropriately during hemodialysis, which is an excellent effect.

This application is a National Stage application of PCT/JP02/06744,filed Jul. 3, 2002, which claims priority from Japanese patentapplication 2001-202818, filed Jul. 3, 2001, and Japanese patentapplication 2002-194447, filed Jul. 3, 2002. The entire contents of eachof the aforementioned applications are incorporated herein by reference.

TECHNICAL FIELD

The present invention relates to a blood treatment apparatus, especiallyto a hemodialysis apparatus which can control water removal conditions,for example water removal speed so as to prevent excessive water removaland also lack of water removal in the contrary, which occur frequentlyduring hemodialysis.

BACKGROUND ART

For treating patients with impaired kidney function, treatments bypurifying blood by dialysis or filtration via semipermeable membranehave been provided conventionally. As for this apparatus, it isimportant to appropriately maintain the blood volume circulating in thepatient body, to perform safe and effective blood purification. A rapidor excessive water removal will decrease excessively patient's bloodcirculating volume, and it may cause reduction of blood pressure, shockor the like. On the contrary, if the water removal is slow, it will takea long time for blood purification, and if sufficient water removalcannot be made, there is a fear that hypertension, heart failure or thelike can occur.

Therefore, a hemodialysis apparatus performing water removal bymonitoring patient's blood condition have been developed. For example,in Japanese Laid-Open Patent Publication No. 6-83723, an estimatingapparatus which estimates the body fluid condition with a Hematocritmeter, and a controlling apparatus which controls the blood pump orultra pressure by the output of said estimating apparatus are described.Concerning this apparatus, it is convenient as the water removal iscontrolled directly according to the measured body fluid condition, buton the other hand, as the water removal is controlled directly by themeasured value, in case the measuring means is not accurate or a troublehappens, it may cause a significant problem. Therefore, in suchfeed-forward control, generally, a separate line independent from thecontrol line is disposed and a safety mechanism is loaded on said line.However, the apparatus becomes complicated when an independent line orsafety mechanism is disposed and the operation becomes difficult.Furthermore, the cost of the apparatus will rise.

Therefore, a simple apparatus as described in Japanese Laid-Open PatentApplication No. 9-149935 was also developed. In other words, whilemonitoring the patient's blood condition, an alarm is ringed dependingto the condition, and the water removal pump is stopped. However, thisapparatus only recognizes if the water removal control is performedunder the same control condition at the time of the initiation ofdialysis, by comparing with the blood concentration measured before theinitiation of dialysis, and it is not possible to perform adequate waterremoval to each patent. Furthermore, if the water removal is notperformed according to the condition, the operator has to adjust eachtime the water removal volume or substitutive fluid volume. Thus, eventhough it was safe, it was complicated and the human cost was high.Moreover, as for said apparatus, a means for measuring the bloodcondition is disposed on the line at the vein fluid side of the bloodcycle, the blood condition after having passed the blood treatmentmachine (dialyser) is measured, thus it may not reflect the patient'sdirect blood condition.

To provide a blood treatment apparatus which have solved the problemsmentioned above, that is, to provide a convenient apparatus at a lowcost by making a structure wherein each patient's blood condition ismonitored, enabling to perform blood treatment adequate to each patientchronologically, by not imposing much burden to the operator during itsuse, and by making the construction of the blood treatment apparatussimple, the present inventors provided a blood treatment apparatus(Japanese Laid-Open Patent Application No. 11-22175), comprising a bloodmeasuring means for measuring blood parameters; a working unit forperforming blood treatment; and a controlling unit controlling theworking unit to perform blood treatment under prescribed blood treatmentcondition, wherein the controlling unit indicates the change of theblood treatment to the working unit, by setting a blood indicationregion determined beforehand against the patient blood indication levelobtained with said blood measuring means, according to the chronologicaltransition of said blood indication level in said blood indicationregion. Furthermore, the present inventors have improved said bloodtreatment apparatus (Japanese Laid-Open Patent Application No.11-22175), and proposed a blood treatment apparatus (Japanese Laid-OpenPatent Application No. 2001-540), wherein by monitoring each patient'sblood condition, the condition of hemodialysis adequate to each patientchronologically, especially the water removal speed can be easilychanged and defined. Said blood treatment apparatus (Japanese Laid-OpenPatent Application No. 2001-540) is a hemodialysis apparatus comprisingat least: (A) a blood measuring means for measuring blood parameter, (B)a working unit for performing blood treatment; and (C) a controllingunit for controlling the working unit to perform blood treatment underprescribed blood treatment condition; wherein the hemodialysis apparatushas a mechanism for controlling the water removal speed, and thecontrolling unit (C) incorporates the blood indicating level obtainedfrom the patients' samples by the blood measuring means (A), monitoringif it transits or not within the defined range defined beforehand ofblood indication level (hereinafter also referred to as defined range ofblood indication level), and when said blood indication level being thetarget to control deviates from said range defined beforehand, the waterremoval speed of the working unit (B) can be changed at a speed ratedefined beforehand.

As for the hemodialysis apparatus mentioned above, it was possible tomanage surely the blood indication level at each point duringhemodialysis treatment, but because it was necessary to define theregion of the target blood indication level at each point, the operationwas complicated. Furthermore, as the defined blood indication level wasdesignated as a range, as long as a blood indication level exists withinthe defined range (even it is at the absolute edge of the range), thecontrol mechanism of the hemodialysis apparatus would not work.Therefore, in case the blood indication level actually measured isslightly missing the point from the target, there was a fear that thecontrol would be delayed.

DISCLOSURE OF THE INVENTION

The object of the present invention is to provide a hemodialysisapparatus having a controlling unit that controls dialysis conditions,for example the water removal speed, so that the blood volume duringhemodialysis can transit appropriately. Moreover, it is to provide ahemodialysis apparatus having improved controlling characteristicswherein the controlling means has a simple mechanism, and is easy tooperate, and on the other hand, can carry out controls speedily andprecisely.

The present invention provides a hemodialysis apparatus (hereinafteralso referred to as first hemodialysis apparatus) that carries outhemodialysis treatment by controlling dialysis conditions, with the useof blood volume (BV level) or blood volume change as an indication level(hereinafter also referred to as blood indication level), wherein thehemodialysis treatment is carried out under dialysis conditionsdetermined by defining the chronological target course of said bloodindication level as a target control line, measuring the bloodindication level at each measurement point (controlling point) in saidchronological course, and calculating the dialysis conditions with theuse of said measured blood indication level and the target bloodindication level at the next measurement point (controlling point) ofsaid measurement point (controlling point), to attain the target bloodindication level at the next measurement point (controlling point).Thus, the object mentioned above was solved.

Furthermore, the present inventors have found that for a hemodialysisapparatus which performs water removal by controlling the blood volumeduring dialysis according to said target control line as said firsthemodialysis apparatus, the blood volume change appears later than thechange of the water removal speed, as it is shown in FIG. 3; and that incase said feed-forward control is carried out by disregarding suchphenomenon that the blood volume change appears later than the change ofwater removal speed, as said feed-forward control is a method that usesthe blood indication level at the measurement point (controlling point)as the control observed level, it attains the next target bloodindication level according to a blood indication level which isdifferent from the blood indication level that is supposed to beattained with the present control level, thus, big changes are observedfor the control levels necessary, for example, the control volumenecessary to calculate the water removal speed, and therefore, thecontrol would not be stable. The present inventors have solved theproblem caused by said control delay by considering said control delayat each control cycle in said feed-forward control.

In other words, the present inventors have improved said feed-forwardcontrol by calculating the forecast of dialysis conditions necessary toattain the next target blood indication level (blood volume change), forexample the forecast for the water removal speed, according to the bloodindication level at the time when the time of control delay have passed.

The improved hemodialysis apparatus is a hemodialysis apparatus(hereinafter also referred to as second hemodialysis apparatus) thatcarries out hemodialysis treatment by controlling dialysis conditions,with the use of said blood indication level as an indication level,wherein the hemodialysis apparatus is able to carrying out control(feed-forward control) being a hemodialysis treatment carried out underdialysis conditions determined by defining the chronological targetcourse of said blood indication level as a control target line,measuring the blood indication level at the control delay point at eachmeasurement point (controlling point) in said chronological course, andcalculating dialysis conditions with the use of said measured bloodindication level and the target blood indication level at the nextmeasurement point (controlling point) of said control delay point, toattain the target blood indication level at the next measurement point(controlling point).

Furthermore, the present inventors have provided a hemodialysisapparatus (hereinafter also referred to as third hemodialysis apparatus)that carries out hemodialysis treatment by controlling dialysisconditions, wherein the hemodialysis apparatus is able to carrying outcontrol (feed-forward control) being a hemodialysis treatment carriedout under dialysis conditions determined by defining the chronologicaltarget course of said blood indication level as a control target-line,calculating the dialysis conditions with the use of each bloodindication level at the two adjacent measuring points (controllingpoints) of said target control line, the water removal speed usedbetween said two measuring points (controlling points), the blood volumeat the time of the initiation of dialysis, and the target bloodindication level determined by said target control line at the nextmeasuring point (controlling point) of said two measuring points(controlling points) so that the blood indication level attains thetarget level at the next measuring level (controlling level). Thus, thepresent inventors have attained the object of the present invention.

The control of said third hemodialysis apparatus (feed-forward control)can be carried out by using the following formula (a).BV ₀{−(% ΔBV _(n−1′)−% ΔBV _(n′))+(% ΔBV _(n′)−% ΔBV _(n+1))}+UFR _(n)×T=UFR _(n+1) ×T  (a)(wherein BV₀ is the blood volume at the time of the initiation ofdialysis; % ΔBV_(n)′ is the blood volume change at an optional selectedmeasurement point (n); % ΔBV_(n−1)′ is the blood volume change at ameasurement point (n−1), which is the previous point of the selectedmeasurement point (n); % ΔBV_(n+1) is the blood volume change defined ata measurement point (n+1), the next measurement point to carry outfeed-forward control; T is the measurement time; UFR_(n) is the waterremoval speed at the selected measurement point (n); UFR_(n+1) is thewater removal speed defined when the control toward the working unit iscarried out, to attain the target blood indication level at ameasurement point (n+1), the next measurement point of the selectedmeasurement point (n).)

Said formula (a) is obtained as follows:

When each measurement point (controlling point) is set as 1, 2 . . .n−1, n, n+1, relational formulae as follows are obtained.

The first measurement point (controlling point) and the secondmeasurement point (controlling point) are:BV ₀[(100% −% ΔBV 1)−(100% −% ΔBV2)]/T=PRR1−UFR1  (1)BV ₀(−% ΔBV _(1′)+% ΔBV ₂′)/T PRR ₁ −UFR ₁  (2)BV ₀(−% ΔBV _(2′)+% ΔBV ₃)/T=PRR ₂ −UFR ₂  (3)

Here, BV₀ is BV level, which is the primary blood volume at the time ofthe initiation of dialysis, % ΔBV₁′ and % ΔBV₂′ are the blood volumechange at the first or second measurement point (controlling point), Tis the elapsed time of dialysis. Moreover, % ΔBV₃ is the blood volumechange determined by the target control line.

Similar relations are obtained at each of any measurement points(controlling point), (n-1) and (n), as it is shown in the followingrelational formulae.BV ₀(−% ΔBV _(n−1′)+% ΔBV _(n′))/T=PRR _(n−1) −UFR _(n−1′)  (4)BV ₀(−% ΔBV _(n′)+% ΔBV _(n+1′))/T=PRR 1−UFR_(n)  (5)

By subtracting said formula (3) from said formula (2), the followingformula (6) is obtained.BV ₀{−(% ΔBV _(1′)−% ΔBV _(2′))−(% ΔBV _(2′)−% ΔBV ₃)}/T=PRR ₁ −PRR ₂+UFR ₂−UFR₁  (6)

When it is hypothecated there is no difference between PRR₁ and PRR₂,that is the distance between the measurement points (controlling point)is defined to be short so as the patient's PPR is not changedsubstantively at each measurement point (controlling point), the firstand second terms in the right side are deleted. Thus, the followingformula (7) is obtained.BV ₀{−(% ΔBV_(1′)−% ΔBV _(2′))+(% ΔBV _(2′)−% ΔBV₃)}/T+UFR ₁ =UFR ₂  (7)

In said formula (7), % ΔBV₃ is the target level at the next measurementpoint (controlling point), and is a level for the blood indication levelto approach by carrying out the control. UFR₂ is the water removal speedto define so that the blod indication level of the next measurementpoint (controlling point) approaches the target level mentioned above.Moreover, BV₀ is the BV level at the time of the initiation of dialysis(primary blood volume), % ΔBV₁′ and % ΔBV₂′ are the blood volume changeat the first or second measurement point (controlling point), and T isthe elapsed time of dialysis.

Said BV₀, % ΔBV₁′, % ΔBV₂′ and T are levels already known, and UFR₁ isalso known as the water removal speed used from the first measurementpoint to the second measurement point (controlling point). Therefore, if% ΔBV₃ to be the target is specified, the water removal speed being adialysis condition can be calculated with the formula (7). The target BVlevel can be determined by the target control line, from the measurementpoint (controlling point). On the contrary, if the hemodialysistreatment is carried out with that water removal speed, the BV level atthe next measurement point (controlling point) can approach the targetlevel, that is the target control line.

When describing the above formula for any measurement points(controlling points) (n) and (n−1), it is shown as the following formula(8), and as described above, the water removal speed to define so thatthe blood indication level approaches the target at the next point,according to the blood volume change at the two measuring points(controlling points); the water removal speed between the twomeasurement points (controlling points); the measurement level for thetime of dialysis T; and the blood volume change defined at the nextmeasurement point (controlling point) of said two measurement points(controlling point) determined according to the target control line ofsaid blood indication level.BV ₀{−(% ΔBV _(n−1′)−% ΔBV _(n′))+(% ΔBV _(n′)−% ΔBV _(n+1))}+UFR _(n)×T=UFR _(n+1) ×T  (8)

In said formula (8), BV₀ is the blood volume at the time of theinitiation of dialysis; % ΔBV_(n)′ is the blood volume change at anoptional selected measurement point (n); % ΔBV_(n−1)′ is the bloodvolume change at the previous measurement point of an optional selectedmeasurement point; % ΔBV_(n+1) is the blood volume change defined at ameasurement point to carry out feed-forward control (next measuringpoint); T is the measured time; UFR_(n) is the water removal speed atthe selected measurement point; UFR_(n+1) is the water removal speeddefined at the next measurement point from the selected measurementpoint (n), when the control is carried out toward the working unit, toattain the target blood indication level.

However, to obtain said formulae (7) and (8), the condition that “thereis no difference between the PRRs at each measurement point (controllingpoint)”, which was hypothecated to derive these formulae, is anassumption, and to meet this condition, it is important that thedistance between each measurement point (controlling point) (ΔT) isdefined to be short so that there is no difference between the PRRs.Moreover, as for this controlling method, errors to the control mayoccur due to errors of BV₀ at the time of the initiation of dialysis,control delay and other factors, but in the actual control, the controlis ensured by defining the water removal speed at each point(measurement point). For example, as it is shown by the graph in FIG. 2,there are substantively no problems for the errors which occur, if thedistance between each measurement point (controlling point) isshortened, and the water removal speed is defined each time.

When considering control delay mentioned above, in the control of saidsecond hemodialysis apparatus, a control carrying out hemodialysistreatment is possible under dialysis conditions calculated by definingthe chronological target course of said blood indication level as atarget control line, with the use of the blood indication level at themeasurement point (controlling point); the blood indication level at thecontrol delay point of the previous measurement point (controllingpoint) adjacent to said measurement point (controlling point); the waterremoval speed used between the measurement point (controlling point) andthe previous point adjacent to said measurement point (controllingpoint); the blood volume at the time of the initiation of dialysis; andthe target blood indication level determined by said target control lineat the next measurement point (controlling point) of said twomeasurement points (controlling point).

In the meantime, a control carried out by using a target control linesuch as that described above, with the use of the blood indication levelat each measuring point, the next target blood indication level of saideach measurement point, or calculated dialysis conditions as parameters,is also called a feed-forward control.

Furthermore, the present inventors have found that said control delayappears significantly at a point wherein said target control linechanges drastically, for example, at a point in the vicinity of thelimit of the former part of dialysis operation, performing dialysisoperation which decreases the blood volume according to the targetcontrol line A as shown in FIG. 1, and the latter part of dialysisoperation, performing dialysis operation to maintain the blood volumesubstantively stable, and that it is possible to solve said problems bythe adapting means as follows, which occur when said control delayappears significantly.

In other words, as for a method to solve said problems, a method ofchanging beforehand the next target at multiple control cycles, justbefore the limit between the former control and the latter control, sothat it approaches to the condition of the target defined line of thelatter part (in the present figure, it is in a horizontal condition), ateach said control cycle. Concretely, it can be exemplified as it isshown in FIG. 4, by a method of moving horizontally the target level forone cycle respectively at each measurement point (controlling point)described above, to moderate the drastic change between the former partand the latter part. In the meantime, said number of control cycleswhich was defined beforehand, can be of any value, as long as it iswithin the range that the object of the present invention can be solved.

Moreover, as for the problem of said control delay, it was also solved,for example, by changing the control line that reduces the drasticchange of the target control line in the vicinity of the limit betweenthe former part and the latter part of dialysis, that is, by changingthe control line that moderates the inclination of the target controlline, and by carrying out the control according to said target controlline that have been changed. Concretely, as shown in FIG. 5, an exampleof carrying out the control by shifting the next target point of themultiple control cycles, in the vicinity of the limit between the formerpart and the latter part of dialysis, to a more latter part of dialysis,can be exemplified.

In the following, examples and methods for calculating the blood volumeto be used as blood indication level or the blood volume change andprimary blood volume for the hemodialysis apparatus of the presentinvention will be explained.

1. Blood Volume (BV) Possible for Use and Blood Volume Change

(1) BV Level

There is no specific limitation for the blood volume that can be used inthe present invention, as long as it shows a blood volume thatcirculates in the patients' body, and Hematocrit level (also referred toas Ht, abbreviated) can be exemplified.

(2) ΔBV level

It refers to the change volume of said blood volume, and is the changevolume of said blood volume per time unit. It can be calculated from Ht,according to the following formula.ΔBV[BV change volume]=(Ht at the time of the initiation of dialysis/Htat the time of measurement)−1(3) % ΔBV

It is the ratio of the blood volume change, and is shown by thefollowing formula.% ΔBV=ΔBV (ΔBV level at the time of measurement)/BV ₀ (BV level at thetime of the initiation of dialysis)×100(4) BV %

It is calculated by dividing the BV level at the time of measurement byBV₀ which is the BV level at the time of the initiation of dialysis(also referred to as primary blood volume) and is expressed inpercentage. It is shown by the following formula.BV%=BV level at the time of measurement/BV ₀ which is BV level at thetime of the initiation of dialysis (primary blood volume)×1002. Definition of Other Parameters and Formulae for Calculating(1) Definition of PRR

PRR is an abbreviation for Plasma Refilling Rate, and is defined asspeed of the blood plasma refilling from the body to the blood vessel,and shows the patient's water removal ability at each point.

(2) Formula for Calculating PRR

PPR is calculated with the following formula:PRR _(n) −UFR _(n) =ΔBV _(n) ′/T _(n)[wherein PRR_(n) is the Plasma Refilling Rate at an optional selectedmeasurement point (n), UFR_(n) is the water removal speed at an optionalselected measurement point (n), ΔBV_(n)′ is the blood volume change atan optional selected measurement point (n), T_(n) is the elapsed timeuntil an optional selected measurement point (n)].

Said blood volume at the time of the initiation of dialysis (primaryblood volume) BV₀ which is the control parameter for the hemodialysisapparatus of the present invention, is the sum of the circulating volumein the body and the circulating volume outside the body, and can becalculated by the following methods for calculating (1) or (2).

(1) Method for Calculating (1)

The first method for calculating the primary blood volume (BV₀) isexplained according to FIG. 6.

At the time of the initiation of dialysis, as the blood volume is notstable, the water removal is not performed, and only the circulationoutside the body is performed. By continuing the circulation outside thebody until the blood volume stabilizes, in case the turgor pressureinside the cells is sufficiently high, and the water run over the cellsand is accumulated up to the cell stroma, it is believed that the bodyfluid (the inflow volume from the cells of FIG. 6) corresponding to theincreased blood volume circulating outside the body (space outside thebody) will move from the cells to the blood vessel. Therefore, it ispossible to obtain the primary blood volume (BV₀) for each patient,according to the following formula with the increased blood volumecirculating outside the body (space outside the body) and % ΔBV.Primary blood volume (BV ₀)=increased blood volume circulating outsidethe body (space outside the body)/% ΔBV.(2) Method for Calculating (2)

The first method for calculating the primary blood volume (BV₀) isexplained according to FIG. 7.

By using the hemodialysis apparatus which controls dialysis conditionsaccording to the blood indication level, only the circulation outsidethe body is performed at the time of the initiation of dialysis as shownin FIG. 7, said circulation outside the body is continued until BV levelstabilizes, and when the BV level becomes stable, dialysis accompaniedby water removal is initiated, and at the same time as said dialysis isinitiated, the water removal is performed with a certain time ΔT (withinthe time PRR does not change), and with a certain water removal speed(water removal speed A), and thus ΔBV₁, which is the change volume ofsaid BV level is calculated. Then, the water removal is performed forthe same time as said certain time ΔT with a different water removalspeed (water removal speed B), and thus, ΔBV₂ which is the change volumeof said BV level, is calculated. Thus, BV₀ can be calculated by usingsaid ΔBV₁, said ΔBV₂, water removal speed A and water removal B.

The primary blood volume (BV₀) of each patient calculated by saidmethod, can be calculated concretely according to the following formula.BV ₀=(water removal speed A−water removal speed B)/(−ΔBV ₁%+ΔBV ₂%)×ΔTSaid formula can be calculated as follows:ΔBV/ΔT=PRR−UFR−ΔBV ₁ /ΔT+ΔBV ₂ /ΔT=water removal speed A−water removal speed BΔBV ₁ =ΔBV ₀[(100%−% ΔBV ₁)−(100%−% ΔBV ₁′)]ΔBV ₂ =ΔBV ₀·% ΔBV ₂BV ₀/ΔT(−% ΔBV₁+% ΔBV₂)=water removal speed A−water removal speed BBV ₀/ΔT=(water removal speed A−water removal speed B)/(−% ΔBV ₁+% ΔBV ₂)

When the BV₀ level which is the primary blood volume is obtained asmentioned above, it is preferable to calculate automatically the targetBV % by using said BV₀ level which is the blood volume inherent to eachpatient and the standard blood volume (BV st) which is definedbeforehand by doctors and the like, according to the following formula(c), and to carry out control with the use of said target BV % as thecontrol object level of the hemodialysis apparatus of the presentinvention. In the meantime, the standard blood volume (BV st) is theblood volume within the range that a healthy person maintains, and it ispreferable to control the hemodialysis apparatus of the presentinvention to approach to the range of this blood volume.Target BV%=standard blood volume (BV st)/primary blood volume (BV₀)×100  (c)

Said standard blood volume (BV st) is a level of the blood volume (BVst) which the patient would have if healthy, defined beforehand bydoctors and the like by considering factors that might influence thehuman blood volume, for example the patient's age, sex, body height andthe like.

Hereinafter, the control line used to control the hemodialysis apparatusof the present invention will be explained.

(1) Target Control Line:

It will be explained according to FIGS. 1 and 2.

In FIG. 1, it is shown by a hatched line A in the former part ofdialysis, and by a horizontal line D in the latter part of dialysis.According to this target control line A of FIG. 1, in the former part ofdialysis, a dialysis operation, for example water removal, whichdecreases the blood volume reasonably to the body is performed, and inthe latter part of dialysis operation, a dialysis operation, for examplewater removal, which maintains the blood volume suitable to each patientaccording to the target control line D, that is, to maintain the bloodvolume substantively constant is performed. Moreover, it is shown by ahatched line A of FIG. 2. The vertical axes of FIGS. 1 and 2 show theblood indication level, for example, % ΔBV level in FIG. 2, and thehorizontal axes show the elapsed time from the initiation of dialysis.Therefore, this target control line is an indication of thechronological course or the target level of the blood indication level,and said target control line is defined before dialysis by doctors andthe like.

(2) Estimated Control Line

It will be explained according to FIGS. 1 and 2.

By using the blood indication level according to the measurement levelssuch as BV, ΔBV or % ΔBV and the like at the measuring point(controlling point) and the target blood indication level shown by saidtarget control line A at the next measurement point (controlling point),the dialysis conditions (for example, the water removal speed) to attainthe target blood indication level at the next measurement point(controlling point) is calculated, and the hemodialysis treatment iscarried out under this calculated dialysis conditions (for example, thewater removal speed), to attain the next measurement point (controllingpoint). As a result, the data line B which will likely slip away fromthe target control line A, will be corrected by the dialysis conditionsnewly defined at every measurement point (controlling point), andtherefore become the estimated control line C, which transits along saidtarget control line A.

(3) Deviated Control Line

The hatched line downward sloping showed beneath the target control lineA of FIG. 1 is the alarm line to function as a deviated control line E.In case dialysis operation is carried out under the control of thehemodialysis apparatus of the present invention, the feed-forwardcontrol will function, but in case the blood indication level exceedssaid deviated control line E, it is preferable to adapt an emergencycontrol different from the standard control method. For example, as itis shown in the graph in FIG. 1, in case the data line B showing thetransition of the data level deviates beneath the alarm line E, thewater removal means such as water removal pump and the like should bestopped, or if necessary, a substitutive fluid to the patient using asubstitutive fluid pump is performed by priority before carrying by thecontrol by feed-forward. Thus, the hemodialysis apparatus of the presentinvention does not only have the function to approach the bloodindication level to the target, but in case the blood indication levelis deviated in a dangerous region, it is possible to ensure the safetyof the patient by preferentially operating the emergency control. Thedefined water removal speed is shown in the bottom half of the graph inFIG. 1.

BRIEF DESCRIPTION OF DRAWINGS

FIG. 1 is a figure explaining the embodiment of dialysis conditions(water removal speed) according to the estimated control line of thehemodialysis apparatus of the present invention.

FIG. 2 is a figure showing the relationship of the target control lineA, data line B and estimated control line C, during the former part ofthe water removal operation using the hemodialysis apparatus of thepresent invention.

FIG. 3 is a figure explaining that the blood volume change (controldelay) appears later than the change of the water removal speed in thehemodialysis apparatus of the present invention.

FIG. 4 explains that to solve the problem of the control delay occurringsignificantly just before the vicinity of the former control part andthe latter control part during control using the hemodialysis apparatusof the present invention, the control is carried out by changing inadvance the next target blood indication level at multiple measurementpoints (controlling points) of control cycle defined beforehand justbefore the limit between the former control and latter control, toapproach the condition of the target definition line of the latter partfor said each control cycle.

FIG. 5 explains that to solve the problem of the control delay occurringsignificantly just before the limit between the former control part andthe latter control part during control, the control line is changed sothat the change of the target control line in the vicinity of the limitbetween the former part and the latter part of dialysis is small, andthe control for the multiple control cycles in the vicinity of the limitbetween the former part and the latter part of dialysis, is carried outaccording to said changed control line.

FIGS. 6 and 7 are figures explaining the method for calculating saidprimary blood volume.

Moreover, in each figures mentioned above, A is the target control line;B is the data line; C is the estimated control line; D is the targetcontrol line; E is the alarm line; F is the urgent liquid supply line;a, b, c, d, e, f, g, h, i, j, k, l, m, n, o and p are water removalspeed; % ΔBV is the blood volume change measured at each measurementpoint (controlling point); and ΔT is the measured cycle (control cycle),respectively.

BEST MODE OF CARRYING OUT THE INVENTION

In the following, embodiments of control for dialysis operation of thepresent invention will be explained according to FIG. 1. In the bottomhalf of FIG. 1, the defined water removal speed is shown.

1. Former Part of Dialysis

(1) Start of Dialysis

When starting dialysis, as the BV level is unstable, the water removalis not performed at the time of the initiation of dialysis (waterremoval speed a=0), only the circulation outside the body is performed,and it is waited for the time interval to pass until the BV levelstabilizes.

(2) The Time of the Initiation of the Measurement

After the BV value is stabilized, the hemodialysis apparatus is resetand the water removal is started. Just after the initiation of waterremoval (first control cycle), as previous control cycle does not exist,and the water removal speed is impossible to predict, the water removalis started without carrying out the control. As for said water removal,BV₀ level inherent to this patient is obtained from the weight beforedialysis, and according to said BV₀ level (primary blood volume), thewater removal speed (b) is calculated to attain the target control lineat the next controlling point, and the hemodialysis is carried out withsaid water removal speed. Then, the feed-forward control is initiatedand the water removal is performed with the water removal speed ((c) to(e)).

In case the water removal speed determined as above mentioned, exceedsthe maximum water removal speed prescribed beforehand, the hemodialysisis carried out with the maximum water removal speed. For example, amongthe water removal speed (a) to (i) shown in FIG. 1, the water removalspeed (d) and (h) exceed the maximum water removal speed line (the blackpart of the water removal speed in the figure), therefore the maximumwater removal speed is used as said water removal speed. In themeantime, when the water removal removal speed exceeds the maximum waterremoval speed, it is most preferable to use the maximum water removalspeed as said water removal speed, but it may be a water removal speedless than the maximum water removal speed. Moreover, as the observedlevel of the blood indication level during dialysis at water removalspeed (f), becomes less than that of the alarm line, the water removalspeed f=0 (that is, water removal is not performed).

As a result of the termination of said water removal, the water removalis started again when the blood indication level exceeds the controlline. The primary water removal speed of control when the water removalis started again, is determined with the same method as for the waterremoval speed (b) mentioned above, and the water removal is performed.When the water removal volume predetermined for the former part ofdialysis has been removed, the control of water removal for the latterpart of dialysis is started.

2. Latter Part of Dialysis

The water removal speed is calculated to finish removing the remainingwater removal volume within the target water removal time, and the waterremoval is performed with said water removal speed. When performingwater removal with this water removal speed, the water removal isstopped in case the blood indication level becomes less than said alarmlevel. For example, when the water removal is performed with the waterremoval speed (j), the blood indication level, for example, the bloodvolume change; became less than said alarm level. Therefore, the waterremoval at the next controlling point is stopped, and the water removalspeed (k) was set to 0. Moreover, as said water removal was stopped, theactual blood volume change ΔBV level have been recovered to be abovesaid alarm level, the water removal speed is calculated so that theremaining water removal volume at that control time is finished to beremoved within the target water removal time (determined water removalvolume), and the water removal is performed with said determined waterremoval speed (1). By performing the water removal with said determinedwater removal speed (1), the actual ΔBV level becomes less than saidalarm level again. Therefore, the water removal at the next controllingpoint is stopped and the water removal speed (m) was set to 0.

Furthermore, as a result of termination of said water removal, as theactual ΔBV level have been recovered to be above the control line, thewater removal speed is calculated so that the remaining water removalvolume at that control time will finish to be removed within the targetwater removal time (determined water removal volume), and the waterremoval is performed with said determined water removal speed (n).However, as the water removal speed (n) of said determined water removalspeed exceeds the maximum water removal speed, the maximum water removalspeed was used as the actual water removal speed. As the target waterremoval volume was not finished removing by the end of the target waterremoval time, the water removal was performed with the maximum waterremoval speed up to the target removal volume, and the dialysis wasfinished.

In the meantime, as for dialysis operation of FIG. 1, the former part ofthe control is carried out by the feed-forward control, but according tothe hemodialysis apparatus of the present invention, the feed-forwardcontrol may also used for the entire control period of dialysisoperation.

INDUSTRIAL APPLICABILITY

According to the present invention, a hemodialysis apparatus havingexcellent effects as follows can be obtained.

-   (1) The control mechanism is simple, and there is little risk of    misoperation or out-of-control.-   (2) As there is no need of difficult installation or unnecessary    operation, the operator can easily operate without difficulty.-   (3) As the control is carried out rapidly and finely, the blood    volume can be transited fairly during the hemodialysis.-   (4) By carrying out a control by considering the control delay, the    control of dialysis conditions can be carried out more exactly.

1. A hemodialysis apparatus, comprising: a blood measuring means thatmeasures a blood parameter, converts the blood parameter into a bloodindex value and conveys to a control member; and an actual workingmember that performs a blood treatment, wherein the control member setsup a target control line which consists of target blood index valuesdetermined previously at each measurement point of a lapsed time ofhemodialysis processing and controls a water removal speed of theworking member by a following formula (a):BV ₀{−(% ΔBV _(n−1′)−% ΔBV _(n′))+(% ΔBV _(n′)−% ΔBV _(n+1))}+UFR _(n)×T=UFR _(n+1) ×T  (a) wherein BV₀ is the blood volume at the time of theinitiation of dialysis; % ΔBV_(n)′ is the blood volume change at anoptional selected measurement point (n); % ΔBV_(n−1)′ is the bloodvolume change at a measurement point (n−1), a point previous to theselected measurement point (n); % ΔBV_(n+1) is the blood volume changedefined at a measurement point (n+1), a next point to carry outfeed-forward control; T is the measurement time; UFR_(n) is the waterremoval speed at a selected measurement point (n); UFR_(n+)1 is thewater removal speed defined when a control toward the working member iscarried out, to attain the target blood indication level at ameasurement point (n+1), a next point of the selected measurement point(n).
 2. The hemodialysis apparatus according to claim 1, wherein thedistance between each point to be measured is defined to be short sothat there is no substantive difference between patients' PRR (PlasmaRefilling Rate: shows the speed of blood plasma that is refilled fromthe body to blood vessel, and is shown by the following formula (b)) ateach point,PRR _(n) −UFR _(n) =ΔBV _(n) ′/T _(n)  (b) wherein PRR_(n) is the PlasmaRefilling Rate at an optional measurement point (n), UFR_(n) is a waterremoval speed at an optional measurement point (n), ΔBV_(n)′ is theblood volume change at an optional measurement point (n), T_(n) is theelapsed time until an optional measurement point (n).
 3. Thehemodialysis apparatus according to claim 2, wherein the distancebetween each point to be measured is defined to be short so that thereis no substantive difference between a patient's water removal abilityat each point.